EP0342278B1 - Méthode de préparation des compositions à deux phases pour accessoires chirurgicaux absorbables - Google Patents

Méthode de préparation des compositions à deux phases pour accessoires chirurgicaux absorbables Download PDF

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Publication number
EP0342278B1
EP0342278B1 EP88304423A EP88304423A EP0342278B1 EP 0342278 B1 EP0342278 B1 EP 0342278B1 EP 88304423 A EP88304423 A EP 88304423A EP 88304423 A EP88304423 A EP 88304423A EP 0342278 B1 EP0342278 B1 EP 0342278B1
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European Patent Office
Prior art keywords
phase
glycolide
polymer
lactide
process according
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EP88304423A
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German (de)
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EP0342278A1 (fr
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Donald S. Kaplan
Matthew E. Hermes
Ross R. Muth
John J. Kennedy
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United States Surgical Corp
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United States Surgical Corp
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Priority to US07/099,635 priority Critical patent/US4744365A/en
Application filed by United States Surgical Corp filed Critical United States Surgical Corp
Priority to DE3855510T priority patent/DE3855510T2/de
Priority to EP88304423A priority patent/EP0342278B1/fr
Priority to AT88304423T priority patent/ATE142236T1/de
Priority to ES88304423T priority patent/ES2091185T3/es
Publication of EP0342278A1 publication Critical patent/EP0342278A1/fr
Priority to US07/562,430 priority patent/US5124103A/en
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Publication of EP0342278B1 publication Critical patent/EP0342278B1/fr
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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/04—Macromolecular materials
    • A61L31/041—Mixtures of macromolecular compounds
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/12—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material
    • A61L31/125—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix
    • A61L31/129—Composite materials, i.e. containing one material dispersed in a matrix of the same or different material having a macromolecular matrix containing macromolecular fillers

Definitions

  • Multi-phase polymeric compositions are shown in Matsuo et al., "Fine Structures of Styrene-Butadiene Block Copolymer Films Cast from Toluene Solution," Polymer , Volume 10, pages 79-87 (1969).
  • lactide/glycolide/related compound polymers or copolymers of small particle size See, e.g., U.S. Pat. Nos. 3,781,349 and 3,846,382.
  • annealing polymers, copolymers, and surgical devices made from lactide and/or glycolide and/or related compounds increases the crystallinity and in vivo tensile strength retention of the polymers, copolymers, and surgical devices. It is also known that the greater the crystallinity, the longer such polymers, copolymers, and surgical devices retain their in vivo tensile strength. See some of the documents first listed, e.g., U.S. Pat. No. 3,636,956 (particularly column 2, line 43 et seq.), 4,137,921 (particularly column 9, lines 61-64), U.K. Appln. No. 2,102,827, and Williams (particularly pages 222-224). It is also known that increasing the crystallinity of such polymers and copolymers makes them more brittle and, thus, decreases their utility as injection molded surgical devices.
  • compositions derived from lactide and glycolide in which lactide moieties predominate have a remarkable and unexpected balance of desirable properties.
  • Those properties include lack of brittleness and the ability to be injection molded and annealed.
  • the properties of the composition make it possible to injection mold surgical devices (e.g., staples, clips) from the composition and to anneal those devices to obtain devices having a remarkable and unexpected balance of desirable properties.
  • substantially amorphous one-phase poly(lactide/glycolide) devices wherein lactide moieties predominate is their occasionally low distortion temperature.
  • Substantially amorphous one-phase poly(lactide/glycolide) devices and compositions therefor are disclosed in commonly-assigned U.S. Pat. No. 4523591. Thus, even the temperature on an extremely hot summer day in Arizona, for example, may be sufficient to cause such devices to deform slightly. Annealing such devices often deforms them so significantly (even if held in a mold during annealing) that they are no longer useful as surgical devices.
  • the new annealed, two-phase device of the same overall composition has a much higher distortion temperature but essentially the same in vivo rate of loss of tensile strength.
  • the present composition makes it possible to increase the resistance to thermal distortion of poly(lactide/glycolide) surgical devices without adversely affecting their rate of loss of tensile strength.
  • the new devices also have surprising resistance to hot wet creep.
  • the step of annealing the new two phase composition increases its crystallinity and tensile strength but decreases (not increases) the time required for it to lose tensile strength in vivo.
  • the present invention relates to a process for making an absorbable surgical device by forming a two-phase polymeric composition, in which a first phase contains lactide polymer and a second phase contains glycolide polymer, forming said surgical device from said polymeric composition, and annealing the surgical device so formed; and the process further comprising the steps of:
  • the process for making a surgical device comprises the steps of:
  • %mol means mole percent and "moiety” means that portion of a polymer derived from a particular monomer.
  • a “glycolide moiety” of a polymer is a portion of the polymer derived from a starting glycolide monomer.
  • substantially amorphous means having 10% or less crystallinity (see, e.g., U.S. Pat. No. 3,878,284, column 3, lines 16-18).
  • “Distortion temperature” means the temperature at which the dimensions of a surgical device start to change significantly because of flow of the material of the surgical device.
  • glycolide and lactide employed in making the new two phase composition can be obtained commercially or may be made using known techniques.
  • a preferred way of making the glycolide is as follows. Hydroxyacetic acid (glycolic acid) is heated under nitrogen to 180°C to remove water. Pressure is then reduced and heating is continued for two hours to yield a prepolymer of polyglycolic acid, which is recovered and powdered.
  • the prepolymer is heated in the presence of Sb 2 0 3 at 275°C under low pressure with an argon purge and stirring.
  • the prepolymer cracks and glycolide is distilled over and recovered in a cold vacuum receiver. Any purification technique that yields pure enough monomers may be used.
  • the glycolide is purified by conventional techniques, such as distillation, crystallization, and sublimation.
  • L-lactide is used alone or in combination with a small amount of the DL racemer.
  • the amount of DL racemer, if used, should be low enough so that crystallization of the lactide rich phase is not inhibited.
  • L-lactide is purified by crystallization from toluene solution.
  • the DL racemer, if used, is purified by crystallization from ethyl acetate.
  • the two phase polymeric lactide/ glycolide composition has a lactide-rich phase having 0 - 25%mol glycolide moieties and a glycolide-rich phase containing lactide and glycolide in amounts such that the composition overall contains up to 45%mol glycolide moieties wherein the lactide-rich phase constitutes at least 50% by weight of the two-phase composition.
  • the lactide-rich phase has 10-20%mol glycolide moieties and the composition overall has 30-45%mol glycolide moieties.
  • the lactide-rich phase has about 10%mol glycolide moieties and the composition overall has about 35%mol glycolide moieties.
  • the two-phase compositions will either comprise a continuous lactide-rich phase interpolymerized with a continuous glycolide-rich phase or will comprise a continuous lactide-rich phase having dispersed throughout it discrete particles of a glycolide-rich phase.
  • the former continuous/continuous
  • continuous/discrete continuous/discrete
  • the lactide-rich phase is the matrix or continuous phase and the glycolide-rich dispersed particles together constitute the dispersed phase.
  • lactide-rich phase and “glycolide-rich” phase mean containing a predominant amount of lactide moieties and containing a predominant amount of glycolide moieties, respectively.
  • the interpolymer two phase polymeric compositions may be made by polymerizing in a first stage a first monomer mixture, adding to the resulting polymer a second monomer mixture, and then in a second stage polymerizing the second monomer mixture while in intimate contact with the polymer of the first stage. Electron scanning micrographs of these compositions show that each phase is continuous, that is, the minor, glycolide-rich phase is continuously interpolymerized within the major lactide rich phase. Any suitable polymerization technique may be used. See, for example, those disclosed in the documents listed above.
  • the polymer resulting from the first-stage polymerization may be recovered, purified, and stored (if necessary) before adding the second monomer mixture to it and carrying out the second-stage polymerization.
  • the first-stage polymerization may be carried out in a reactor and then, without recovering or purifying the resulting polymer, the second monomer mixture may be added to the same reactor and the second-stage polymerization carried out.
  • the second scheme has fewer steps than the first scheme (because of the elimination of recovery, purification, and possible intermediate storage), but the first scheme allows for better quality control of the characteristics of the intermediate polymeric product. Which scheme is used will depend upon a variety of factors, including cost and the need to control the characteristics of the intermediate polymeric product.
  • Recovery and purification of the intermediate polymer from the first reaction stage (if desired) and recovery and purification of the final polymer from the second reaction stage are accomplished in the following manner.
  • the reaction product is isolated (e.g., removed from the reactor) comminuted, and treated to remove residual reactants.
  • Polymer particle size is usually a few millimeters. Particles too small are undesirable.
  • a sufficient amount of unreacted monomer is removed so that the annealed surgical device and the annealable polymeric composition have the desired properties (e.g., high enough distortion temperature and a high enough molecular weight).
  • Any method capable of removing the unreacted monomers may be used, provided that method results in the polymeric product having the desired properties and does not adversely affect any other important properties of the final polymer.
  • the preferred purification procedure is as follows.
  • the crude-reaction product is contacted with ethyl ether for about 72 hours in a Soxhlet-type extractor to remove unreacted monomer. Typically, in each stage 4-10% of the starting monomers remain unreacted.
  • the partially purified polymer is slowly heated under vacuum from ambient temperature to 130°C over a period of about 100 hours.
  • the slow rate of heating is important to prevent melting (strictly speaking, flowing together) of the copolymer particles and to remove any water present.
  • Dry inert gas may be used to purge the system, and occasionally the heating step may require more than 100 hours for the polymer to reach the desired properties. This procedure removes any residual solvent (ethyl ether) present.
  • the purified copolymer After removal of unreacted monomers (and of solvent, if solvent extraction is used), the purified copolymer must be dried if it was not dried enough in the monomer removal step and, in any event, stored to keep it dry.
  • the intermediate and final polymers must be as dry as possible before forming surgical devices from the final composition because the presence of too much water in the polymers results in inherent viscosity (molecular weight) dropping below the minimum acceptable levels during forming the surgical device.
  • the polymers be dried to a dry state and stored at a relative humidity of no more than a few percent.
  • the purified dried polymers (intermediate, if any, and final) are stored under a vacuum and/or with a dry inert gas pad.
  • the length of storage affects the allowable relative humidity for storage, higher humidity levels being more acceptable if storage is to be for a shorter period of time.
  • the two-phase composition having a continuous lactide-rich phase and a discrete particle glycolide-rich phase may be made by forming the polymers of the two phases separately and then mixing small particles of the glycolide-rich polymer into the lactide-rich polymer. Mixing may be accomplished in conventional equipment (provided the polymeric materials are kept dry enough), for example, in the surgical device-forming equipment.
  • Each polymer may be made separately in the manner described above and then the glycolide-rich polymer comminuted to a fine particle size (generally 10 microns or less) before mixing. Smaller particles give better results. A long grinding period is usually disadvantageous because during grinding, the glycolide-rich polymer may pick up too much moisture from the ambient atmosphere (even if grinding is performed in a dry room), and that will adversely affect the properties of the final device. Accordingly, it is preferred that the glycolide-rich phase be polymerized using a technique that results in the particles being small enough so that a comminuting step is relatively short or not needed at all.
  • the absorbable devices are made preferably by injection molding the final, purified, two-phase polymeric composition using, for example, a screw injection molding machine.
  • the resulting devices have a first phase containing 0 - 25%mol glycolide moieties and an overall composition of up to 45%mol glycolide moieties and the first phase constitutes at least 50% and not more than 95% by weight of the devices.
  • a preheated vacuum hopper retrofitted to the screw injection molding machine has been found to be useful for maintaining the purified dried copolymer in a dry condition.
  • the vacuum hopper comprises a vessel upstream of the machine's standard hopper. The vessel must be capable of operating under vacuum and of being heated.
  • the preferred procedure for injection molding the devices is to place the purified dried copolymer particles in the vacuum hopper under a vacuum, heat the hopper to 50-70°C, and hold temperature and vacuum for at least an hour, preferably about 15 hours.
  • the pressure in the vacuum hopper is desirably no higher than 667 Pa (5 mm Hg) and preferably no higher than 13.3 Pa (0.1 mm Hg).
  • the standard hopper must also be heated and dried before allowing the purified, dried two-phase polymeric composition to pass from the vacuum hopper into the standard hopper.
  • the entire injection molding system desirably is padded and/or purged with a dry inert gas.
  • Injection molding is generally carried out at a temperature below the melting point of the glycolide-rich phase.
  • the design of the surgical devices is not critical insofar as the present invention is concerned.
  • the devices may, for instance, be staples or clips. Examples of staples and clips which can be made from the polymers of this invention are shown in U.S. Pat. Nos. 4,060,089; 4,402,445; 4,492,232 and 4,512,345. Other possible device designs will be known to those skilled in the art.
  • the formed devices are then annealed (or heat-treated), preferably while held in restraining fixtures, e.g., molds. Holding them in restraining fixtures prevents the annealing step from deforming the devices.
  • the devices are held at 80 to 130°C for from 10 to 120 minutes, shorter times being used with higher temperatures.
  • the temperature may be held constant at a single value or held constant at two or more values in stages.
  • the devices are annealed preferably by keeping them at about 90°C for about 90 minutes.
  • Injection molding reduces the crystallinity of the lactide-rich phase from 5-10% to about zero but usually has no effect on the crystallinity of the glycolide-rich phase, which is about 1.5%.
  • Annealing imparts crystallinity to the lactide-rich phase (raising it to about 10-20%) but has little effect on the glycolide-rich phase (crystallinity rises, if at all, to a maximum of about 10%).
  • a preferred procedure for making the two-continuous-phase composition according to the first scheme is as follows. This discussion describes manufacture of a particular composition having about 1O%mol glycolide in the lactide-rich phase and about 30%mol glycolide moieties overall. The quantities of reactants given may be varied depending on the particular composition desired.
  • Lactide (5,620 grams) and glycolide (503 grams) are charged to a reactor under an argon blanket.
  • a solution of stannous octoate catalyst in diethyl ether is added to give 0.02%mol of catalyst, based on the total weight of lactide and glycolide.
  • Sufficient initiator (pure glycolic acid) is added to control the molecular weight so the desired inherent viscosity is achieved.
  • the reactor is further purged with argon and held at 5 psi (34.5 kPa) while heating to 170-175°C. Pressure and temperature are maintained for six hours.
  • the reaction product is then recovered and purified in the manner described above.
  • the intermediate polymeric product is carefully dried in a vacuum oven at an ambient pressure of ⁇ 133.3 Pa ( ⁇ 1 mm Hg) by heating at 70°C for 6 hours and then 100°C for 6 hours.
  • the polymer is allowed to cool to ambient temperature in the vacuum oven.
  • the initial inherent viscosity of the copolymer should be at least 1.9, preferably 2.2. Lower inherent viscosities (e.g., 1.3) may be used if the polymeric product is kept very dry up through the device-forming step. After forming the absorbable surgical device, the inherent viscosity of the device should be ⁇ 1.0, preferably ⁇ 1.2.
  • Inherent viscosity is measured at 30°C at a concentration of 0.25 g of polymer/dl of solution in a suitable solvent, such as chloroform for the first-stage polymer or hexafluoroisopropanol for the two-phase composition, using a Ubbelohde viscometer.
  • a suitable solvent such as chloroform for the first-stage polymer or hexafluoroisopropanol for the two-phase composition
  • the vacuum in the oven is released by bleeding in argon.
  • the copolymer is quickly loaded into the reactor while argon is flowing through the reactor.
  • the reactor is sealed, pressurized to about 34.5 kPa (5 psi), and connected to a temperature controller, hot oil circulator, and an argon tank.
  • the settings on the temperature controller and hot oil circulator are maintained at about 180-190°C.
  • stirring is started.
  • 320 grams of purified glycolide are added (430 grams of glycolide if the preferred composition with an overall content of 35%mol glycolide moieties is to be made).
  • the reactor When glycolide addition is completed, the reactor is resealed, repressurized, and the stirring rate is increased. When the pot temperature reaches 180°C, the stirring rate is reduced. If the pot temperature continues to rise, the oil bath temperature is reduced to 175°C. 30-60 minutes after addition of the glycolide is complete, the two-phase polymer composition is removed from the reactor and is ground, dried, and ether extracted as described above.
  • purified L-lactide (1,362 grams, 9.4583 gmoles) with 0.02% by weight stannous octoate is placed in a clean and dry reactor (the same type of conical/vertical reactor as described above), which is then sealed and pressurized to about 34.5 kPa (5 psi) with a dry, inert gas (argon or nitrogen).
  • the lactide is polymerized for 14 hours at 155-160°C.
  • the temperature is then raised to 175-180°C and 731.4 grams (6.3056 gmoles) of purified glycolide are added.
  • the mixture is vigorously stirred until the temperature rises to 180°C and then stirring is slowed to a low speed.
  • the reaction mixture is held at 180-185°C for 50-60 minutes, and then the two phase polymer is removed from the reactor, ground, and extracted as described above to remove residual monomer.
  • the overall molar ratio of monomers used is 40/60 glycolide/L-lactide.
  • the glycolide content of the lactide-rich phase is about 5%mol and the overall glycolide content of the final, two phase composition is about 40%mol.
  • purified L-lactide (1,250.1 grams, 8.6813 gmoles) and purified glycolide (111.9 grams, 0.9646 gmoles) with 0.02% by weight stannous octoate are placed in a clean and dry conical/vertical reactor, which is then sealed and pressurized to about 34.5 kPa (5 psi) with a dry, inert gas (argon or nitrogen).
  • the mixture is polymerized for 14 hour at 155-160°C.
  • the temperature is then raised to 175-180°C and 430.4 grams of purified glycolide (3.7103 gmoles) are added.
  • the mixture is vigorously stirred until the temperature rises to 180°C and then stirring is slowed to a low speed.
  • the reaction mixture is held at 180-185°C for 30-60 minutes and then the copolymer is removed from the reactor, ground, and extracted as described above to remove residual monomer.
  • the overall molar ratio of monomers used is 35/65 glycolide to L-lactide.
  • the glycolide moiety content of the lactide-rich phase is about 10%mol and the overall glycolide moiety content of the final, two-phase composition is about 35%mol.
  • the discrete phase is preferably 100% polyglycolic acid (i.e., 100%mol derived from glycolide moieties) of small particle size (generally less than 10 microns).
  • a preferred way of making those particles is as follows. This discussion assumes manufacture of a specific quantity of small particle size polyglycolic acid. Other quantities may be made by modifying the procedure.
  • thermowell for a thermocouple is placed in the fourth neck for temperature control.
  • the toluene is heated to 100°C (with stirring). 500 to 520 grams of pure glycolide are added and the solution temperature is brought back up to 100°C. 3 grams of stannous octoate in 10 cc of toluene are added via syringe. The reaction mixture should be well stirred. A white precipitate will form within a few minutes.
  • a well-mixed solution of 10 grams of stannous octoate, 10 grams of lauryl alcohol, and 80 cc of toluene is prepared and 10 cc of it are added via syringe to the reaction mixture every 30 minutes.
  • the heating mantle is removed from the reaction flask after the last addition and the reaction mixture is allowed to cool to approximately 50°C.
  • a fine white powder will be dispersed in the reaction mixture.
  • the powder is recovered by filtration and extracted with boiling acetone for 15 minutes.
  • the powder is filtered and washed with ethyl ether.
  • the ether is removed from the powder by vacuum filtration and the powder is dried in a vacuum oven at 100°C and less than 1.33 kPa (10 mm Hg) for about 10-15 hours.
  • the powder is comminuted in a ball mill with 7-10 ceramic balls for about 1 hour.
  • the ground particles are screened to remove any large agglomerates and are then blended with a lactide-rich polymer and injection molded to form the surgical devices.
  • Table I shows the tensile strengths of the hinge portion, the crystallinities (as measured by x-ray diffraction), the approximate distortion temperatures, and the times to failure in hot-wet creep tests of surgical clips having essentially the configuration shown in U.S. Pat. No. 4,512,345 made of different annealed and unannealed two-phase compositions and of two "control" compositions.
  • Each control composition is a one-phase, substantially amorphous material made by the method disclosed in U.S. Pat. No. 4,523,591.
  • Control composition I contains approximately 20%mol glycolide moieties and 80%mol lactide moieties and control composition II contains approximately 30%mol glycolide moieties and 70%mol lactide moieties.
  • the tensile strengths were measured using an Instron tester at a crosshead speed of 0.02 inches per minute (0.5 mm/min).
  • the time to failure in the hot wet creep test is the time required for the clip to fail, that is, allow air to pass through an externally clipped flexible tube, when the tube is subjected to an internal 13.8 kPa (2 psi) pressure applied at one-hour intervals.
  • results show that annealing significantly increases the tensile strength of surgical devices made from the two phase composition.
  • results also show that annealing has little effect on the crystallinity of the glycolide-rich phase but a significant effect on the crystallinity of the lactide-rich phase.
  • results also show that annealed surgical devices made of the multiphase composition have significantly higher distortion temperatures than devices made of a substantially amorphous composition having the same overall composition (compare Control II with "1030 annealed”).
  • results also show the superior hot-wet creep resistance of the annealed devices of this invention.
  • the following table shows how annealing affects the rate of loss of peak tensile strength of surgical staples made using the compositions of this invention and made using the control compositions.
  • the staple configuration is substantially the same as that shown in U.S. Pat. Appln. No. 480,423, filed March 30, 1983.
  • Instron tester for the in vitro tests, staples were implanted in abdominal and muscular tissues in rats (two staples per rat).
  • the composition has been described as being two-phase. It is possible that three or more stages of monomer addition and polymerization could be used.
  • the resulting multi-phase polymer would then have more than two phases. However, it still should have a lactide-rich first phase constituting at least 50% by weight of the total composition and have no more than about 25%m glycolide moieties.
  • the two or more other phases would then have lactide and glycolide moieties in amounts such that the overall multi-phase composition had no more than about 45%m glycolide moieties.
  • Another possible variation when preparing an interpolymer composition is to use the crude multi-phase polymeric composition from the final polymerization stage (without any purification) for making the surgical devices.
  • Another possible variation is to interpolymerize several continuous phases, but also add one or more discrete phases.

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Claims (12)

  1. Procédé de fabrication d'un dispositif chirurgical absorbable en formant une composition polymérique à deux phases où une première phase contient un polymère de lactide et une seconde phase contient un polymère de glycolide, en formant ledit dispositif chirurgical à partir de ladite composition polymérique et en recuisant le dispositif chirurgical ainsi formé; et le procédé comprenant de plus les étapes de :
    - prévoir jusqu'à 25% en moles d'entités de glycolide dans la première phase et au moins 75% en moles d'entités de lactide dans la première phase; et
    - prévoir la première phase en une quantité suffisante pour constituer au moins 50% en poids du dispositif chirurgical recuit; et où
    - la composition polymérique ne contient pas plus de 45% en moles d'entités de glycolide et la première phase constitue moins de 95% en poids du dispositif chirurgical recuit.
  2. Procédé selon la revendication 1 caractérisé en ce que la première phase est formée en polymérisant un premier mélange de monomères contenant au moins 75% en moles de lactide jusqu'à ce que la polymérisation soit sensiblement terminée et on ajoute, à la première phase, un second mélange de monomères comprenant du glycolide et le second mélange de monomères est polymérisé en présence du premier polymère pour ainsi former un second polymère ayant deux phases.
  3. Procédé selon la revendication 2 où le premier polymère est récupéré et purifié avant d'ajouter le second mélange de monomères.
  4. Procédé selon la revendication 1 où la première phase est formée en polymérisant un premier mélange de monomères contenant au moins 75% en moles de lactide jusqu'à ce que la polymérisation soit sensiblement terminée et on ajoute à la première phase un second polymère contenant une quantité prédominante d'entités de glycolide sous la forme de particules distinctes.
  5. Procédé selon l'une quelconque des revendications précédentes où la seconde phase contient une quantité prédominante d'entités de polymère de glycolide.
  6. Procédé selon l'une quelconque des revendications précédentes où la seconde phase est dispersée dans la première phase.
  7. Procédé selon l'une quelconque des revendications précédentes où ledit dispositif est formé en utilisant une machine de moulage par injection.
  8. Procédé selon la revendication 7, la machine ayant une trémie préchauffée d'alimentation et un appareil de moulage par injection à vis qui lui est attaché, le procédé comprenant les étapes de maintenir la composition dans une trémie chauffée à vide; de faire passer la composition à la trémie préchauffée d'alimentation; d'introduire la composition de la trémie d'alimentation à l'appareil de moulage par injection à vis; et de récupérer l'article moulé.
  9. Procédé selon l'une quelconque des revendications précédentes où l'étape de former le dispositif chirurgical est effectué à une température inférieure au point de fusion du polymère de la phase riche en glycolide.
  10. Procédé selon l'une quelconque des revendications précédentes où l'étape de recuit est effectuée à une température comprise entre 80°C et 130°C et pendant un temps compris entre 10 et 120 minutes.
  11. Procédé selon l'une quelconque des revendications précédentes caractérisé en ce que la composition polymérique est maintenue en une condition sèche avant de former le dispositif chirurgical.
  12. Procédé selon l'une quelconque des revendications précédentes où le dispositif chirurgical est une pince ou une agrafe.
EP88304423A 1984-03-06 1988-05-16 Méthode de préparation des compositions à deux phases pour accessoires chirurgicaux absorbables Expired - Lifetime EP0342278B1 (fr)

Priority Applications (6)

Application Number Priority Date Filing Date Title
US07/099,635 US4744365A (en) 1986-07-17 1987-09-22 Two-phase compositions for absorbable surgical devices
DE3855510T DE3855510T2 (de) 1984-03-06 1988-05-16 Ein Verfahren zur Herstellung von zwei-Phasen-Zusammensetzungen für absorbierbare chirurgische Ausrüstungen
EP88304423A EP0342278B1 (fr) 1984-03-06 1988-05-16 Méthode de préparation des compositions à deux phases pour accessoires chirurgicaux absorbables
AT88304423T ATE142236T1 (de) 1984-03-06 1988-05-16 Ein verfahren zur herstellung von zwei-phasen- zusammensetzungen für absorbierbare chirurgische ausrüstungen
ES88304423T ES2091185T3 (es) 1984-03-06 1988-05-16 Un procedimiento para la preparacion de composiciones bifasicas para dispositivos quirurgicos absorbibles.
US07/562,430 US5124103A (en) 1984-03-06 1990-08-02 Two phase compositions for absorbable surgical devices

Applications Claiming Priority (5)

Application Number Priority Date Filing Date Title
US58668684A 1984-03-06 1984-03-06
US86030286A 1986-07-17 1986-07-17
US11746687A 1987-11-05 1987-11-05
EP88304423A EP0342278B1 (fr) 1984-03-06 1988-05-16 Méthode de préparation des compositions à deux phases pour accessoires chirurgicaux absorbables
US07/562,430 US5124103A (en) 1984-03-06 1990-08-02 Two phase compositions for absorbable surgical devices

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EP0342278A1 EP0342278A1 (fr) 1989-11-23
EP0342278B1 true EP0342278B1 (fr) 1996-09-04

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EP (1) EP0342278B1 (fr)
AT (1) ATE142236T1 (fr)
DE (1) DE3855510T2 (fr)
ES (1) ES2091185T3 (fr)

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Also Published As

Publication number Publication date
EP0342278A1 (fr) 1989-11-23
ATE142236T1 (de) 1996-09-15
US5124103A (en) 1992-06-23
ES2091185T3 (es) 1996-11-01
DE3855510D1 (de) 1996-10-10
DE3855510T2 (de) 1997-02-06

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